Perfusion bioreactor, perfusion device, artificial liver system, and related methods

ABSTRACT

A perfusion bioreactor and a perfusion device. Each perfusion device has a mesh structure, and an encapsulated organ tissue (EOT) disposed in the mesh structure. The EOT has a body with a thickness defined between a first surface of the body and a second surface of the body. The body has at least one channel extending into the body from one of the first and second surfaces to receive a fluid therein. The at least one channel has a diameter selected to diffuse solutes out of the fluid and into the body. The perfusion devices are arranged one adjacent to another and spaced apart from each other along the length of the bioreactor to receive fluid, and to perfuse the fluid to the EOT of each perfusion device and to the at least one channel therein. A method of processing blood plasma and an artificial liver system are also disclosed.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.11,096,388 filed May 22, 2019 which is a National Phase Entry of PCTApplication No. PCT/CA2019/050698 filed May 22, 2019, which claimspriority to U.S. provisional patent application No. 62/674,696 filed May22, 2018, the entire contents of all of which are incorporated byreference herein.

TECHNICAL FIELD

The application relates generally to organ replacement therapy and, moreparticularly, to reactors, devices, and systems for performing same.

BACKGROUND

Acute liver failure (ALF) is characterized by an abrupt decrease inhepatic function following a severe insult to the liver in patients withno pre-existing liver disease. A standard treatment for acute liverfailure is liver transplantation, which should be carried out within afew days from the onset of symptoms to avoid the progression tomulti-organ failure. Liver transplantation is difficult, risky and notwidely available. The liver's regenerative abilities are well documentedin the literature. Since patients with ALF often do not have anyunderlying disease prior to the injury, approximatively 80% oftransplants might be avoided if liver function could be replaced for thetime needed for the liver to regenerate, such as with an extracorporealsystem.

Some extracorporeal systems to treat liver failure are cell-free liversupport systems, which are based on molecular adsorption and albumindialysis to purify the blood. The systems are usually used inconjunction with hemodialysis to remove water soluble solutes. However,clinical trials have shown no significant differences in patientsurvival between standard therapy and some approved extracorporealsystems.

Some cell-based dialysis systems are under investigation. The use ofhuman liver cells is favored since it circumvents unwanted effectsassociated with the use of xenogeneic liver cells. However, human livercells are limited in availability, difficult to culture and some haveshown rapid decrease in liver specific functions with time. Anotherlimitation of some of the devices is the limited mass exchange betweenthe patient's blood and the extracorporeal liver cells.

SUMMARY

There is provided a perfusion bioreactor, comprising: a housing having alength defined between a housing inlet and a housing outlet, the housinghaving an inner surface delimiting an internal cavity of the housingdisposed between the housing inlet and the housing outlet and in fluidcommunication therewith; and perfusion devices disposed in the internalcavity of the housing, each of the perfusion devices comprising: a meshstructure supported from the inner surface of the housing, the meshstructure having a first wall spaced apart from a second wall to definean internal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated organ tissue disposed in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated organ tissue having at least one organoid atleast partially covered with a biocompatible cross-linked polymer, theencapsulated organ tissue having a body with a thickness defined betweena first surface of the body adjacent the first wall of the meshstructure and a second surface of the body adjacent the second wall ofthe mesh structure, the body having at least one channel extending intothe body from one of the first and second surfaces to receive a fluidtherein, the at least one channel having a diameter selected to diffusesolutes out of the fluid and into the body; the perfusion devices beingdisposed in the internal cavity of the housing one adjacent to anotherand spaced apart from each other along the length of the housing toreceive the fluid conveyed from the housing inlet to the housing outlet,and to perfuse the fluid to the encapsulated organ tissue of eachperfusion device and to the at least one channel therein.

There is provided a perfusion device, comprising: a mesh structurehaving a first wall spaced apart from a second wall to define aninternal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated organ tissue disposed in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated organ tissue having at least one organoid atleast partially covered with a biocompatible cross-linked polymer, theencapsulated organ tissue having a body with a thickness defined betweena first surface of the body adjacent the first wall of the meshstructure and a second surface of the body adjacent the second wall ofthe mesh structure, the body having at least one channel extending intothe body from one of the first and second surfaces to receive a fluidtherein, the at least one channel having a diameter selected to diffusesolutes out of the fluid and into the body.

There is provided an artificial liver system, comprising: a fluidnetwork and a pump to circulate plasma through the fluid network; and aperfusion bioreactor in fluid communication with the fluid network toreceive the plasma therefrom, the perfusion bioreactor comprising: ahousing having a length defined between a housing inlet and a housingoutlet, the housing having an inner surface delimiting an internalcavity of the housing between the housing inlet and the housing outletand in fluid communication therewith, the housing inlet receiving theplasma; and a plurality of perfusion devices disposed in the internalcavity of the housing, each of the perfusion devices comprising: a meshstructure supported from the inner surface of the housing, the meshstructure having a first wall spaced apart from a second wall to definean internal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated liver tissue disposed in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated liver tissue having at least one liverorganoid at least partially covered with a biocompatible cross-linkedpolymer, the encapsulated liver tissue having a body with a thicknessdefined between a first surface of the body adjacent the first wall ofthe mesh structure and a second surface of the body adjacent the secondwall of the mesh structure, the body having at least one channelextending into the body from one of the first and second surfaces toreceive the plasma therein, the at least one channel having a diameterselected to diffuse undesired solutes out of the plasma and into thebody; the perfusion devices being disposed in the internal cavity of thehousing one adjacent to another and spaced apart from each other alongthe length of the housing to receive the plasma conveyed from thehousing inlet to the housing outlet, and to perfuse the plasma to theencapsulated liver tissue of each perfusion device and to the at leastone channel therein.

There is provided a method of processing blood plasma, comprising:conveying the blood plasma to at least one channel formed in anencapsulated liver tissue having at least one liver organoid at leastpartially covered with a biocompatible cross-linked polymer, the atleast one channel having a diameter selected to diffuse undesiredsolutes out of the blood plasma and into the encapsulated liver tissue.

There is provided a method of making a perfusion device, comprising:providing at least one liver organoid at least partially covered with abiocompatible cross-linked polymer, the at least one liver organoid atleast partially covered with the biocompatible cross-linked polymerhaving a body with at least one channel extending into the body, the atleast one channel having a diameter selected to diffuse solutes out of afluid and into the body; and positioning the body within a cavity of amesh structure to allow the fluid to enter the cavity and the at leastone channel of the body, and to exit the cavity.

DESCRIPTION OF THE DRAWINGS

Reference is now made to the accompanying figures in which:

FIG. 1A is a schematic view of a perfusion bioreactor;

FIG. 1B is a schematic view of a housing and perfusion devices of theperfusion bioreactor of FIG. 1A;

FIG. 2A is a perspective view of part of a mesh structure of theperfusion devices of FIG. 1B;

FIG. 2B is a perspective view of another part of the mesh structure ofFIG. 2A;

FIG. 3 is a perspective view of another mesh structure for use in theperfusion devices of FIG. 1B;

FIG. 4 shows a process for encapsulating liver organoids and making anencapsulated liver tissue for use in the perfusion devices of FIG. 1B;

FIG. 5A is a perspective view of one of the perfusion devices of FIG.1B;

FIG. 5B is a side elevational view of an encapsulated organ tissue ofthe perfusion device shown in FIG. 5A;

FIG. 5C is an end view of the encapsulated organ tissue of the perfusiondevice shown in FIG. 5A;

FIG. 5D is a side elevational view of the encapsulated organ tissues oftwo of the perfusion devices of FIG. 1B arranged adjacent to each other;

FIG. 6 is a side elevational view of another encapsulated organ tissuefor use in the perfusion devices of FIG. 1B;

FIG. 7 is a side elevational view of another an encapsulated organtissue for use in the perfusion devices of FIG. 1B;

FIG. 8 is a schematic view of an artificial liver system having theperfusion bioreactor of FIG. 1A;

FIG. 9 is a schematic view of another artificial liver system having theperfusion bioreactor of FIG. 1A;

FIG. 10 is a schematic view of another artificial liver system havingthe perfusion bioreactor of FIG. 1A;

FIG. 11A is a schematic view of another perfusion bioreactor;

FIG. 11B is a perspective view of an internal support for the perfusionbioreactor of FIG. 11A; and

FIG. 11C is a perspective view of the internal support of FIG. 11B withperfusion devices.

DETAILED DESCRIPTION

FIG. 1A illustrates a perfusion bioreactor 10. The perfusion bioreactor10 is an apparatus in which a perfusion operation is carried out.Specifically, the perfusion bioreactor 10 (sometimes referred to hereinsimply as the “bioreactor 10”) allows for the exchange of particlesbetween a liquid and the cells and tissues embedded within a porousbiomaterial. The bioreactor 10 is a vessel having a controlledenvironment that allows cells to survive and perform metabolicactivities. In the depicted embodiment, and as explained in more detailbelow, the bioreactor 10 has agglomerations of organ cells which performat least part of the metabolic functions of an organ of the human body.The bioreactor 10 may be manufactured from any suitable biocompatibleplastic, metal, or composites thereof, for example polycarbonate, inorder to achieve this functionality.

In operation, the bioreactor 10 receives fluid, and conveys fluid out ofthe bioreactor 10. The bioreactor 10 therefore has a suitable inlet anda suitable outlet that are connected to suitable tubing. In the depictedembodiment, the bioreactor 10 has a housing 16 which is an elongatedbody extending a length L between a housing inlet 18A and a housingoutlet 18B. The housing inlet 18A is configured to allow for infusion ofplasma, nutrients, or other fluid materials into the housing 16. In thedepicted embodiment, the housing 16 is a cylindrical body extendingalong a longitudinal axis such that it is longer than it is wide. Othershapes of the housing 16 are possible and within the scope of thepresent disclosure. The housing inlet and outlet 18A, 18B are conicalends of the housing 16, and act as funnels to convey fluid into and outof the main portion of the housing 16. The housing 16 is hollow, andthus has an inner cavity 19 into which the fluid is conveyed forinteraction with the organ cells. The inner cavity 19 is delimited by awall of the housing, which is cylindrical in the depicted embodiment,and which defines an inner surface 19A. Fluid travels through thehousing 16 by first entering the housing inlet 18A, then travellingthrough the inner cavity 19, and the exiting via the housing outlet 18B.

Referring to FIG. 1B, the bioreactor 10 also includes perfusion devices20. Each perfusion device 20 performs the work of the bioreactor 10 byassisting with the exchange of particles between a liquid and the cellsand tissues embedded within a porous biomaterial of each perfusiondevice 20. The perfusion devices 20 contain the agglomeration of organcells which perform at least part of the metabolic functions of an organof the human body, as explained in greater detail below. The perfusiondevices 20 are disposed in the internal cavity 19 of the housing 16. Asshown in FIG. 1B, the perfusion devices 20 are disposed in the internalcavity 19 one adjacent to another and spaced apart from each other alongthe length L of the housing 16. The perfusion devices 20 form a stack ofperfusion devices 20A. In the depicted embodiment, the stack ofperfusion devices 20A has an upright or vertical orientation. Theperfusion devices 20 are stacked one on top of the other in the stack ofperfusion devices 20A. In an alternate embodiment, the stack ofperfusion devices 20A has a horizontal or inclined orientation.Irrespective of their orientation, the perfusion devices 20 and theircomponents interact with the fluid which travels through the innercavity 19 of the housing 16, from the housing inlet 18A to the housingoutlet 18B.

Still referring to FIG. 1B, each perfusion device 20 includes a meshstructure 30 and one or more encapsulated organ tissues 40. The meshstructure 30 forms the corpus of the perfusion device 20 and providesstructure thereto. The mesh structure 30 is porous, and is supportedfrom the inner surface 19A of the housing 16 to mount each perfusiondevice 20 to the housing 16. The encapsulated organ tissue 40 of eachperfusion device is positioned within the mesh structure 30. The meshstructure 30 is therefore any suitable device for holding theencapsulated organ tissue 40, and for allowing the fluid within thehousing 16 to engage the encapsulated organ tissue 40.

Another embodiment of the bioreactor 600 is shown in FIGS. 11A to 11C.In the depicted embodiment, the bioreactor 600 has a housing 616 whichis an elongated body extending a length between a housing inlet 618A anda housing outlet 618B. In the depicted embodiment, the housing 616 is acylindrical body extending along a longitudinal axis such that it islonger than it is wide. The housing 616 is transparent and admits light.The housing inlet and outlet 618A, 618B are conical ends of the housing616, and act as funnels to convey fluid into and out of the main portionof the housing 616. The housing 616 is hollow, and thus has an innercavity 619 into which the fluid is conveyed for interaction with theorgan cells. The inner cavity 619 is delimited by a transparent wall ofthe housing 616, which is cylindrical in the depicted embodiment. Fluidtravels through the housing 616 by first entering the housing inlet618A, then travelling through the inner cavity 619, and the exiting viathe housing outlet 618B.

Still referring to FIGS. 11A to 11C, the bioreactor 600 has an internalsupport 617 for supporting the perfusion devices 20. The internalsupport 617 is positioned within the inner cavity 619. The internalsupport 617 includes end plates 617A which are perforated to permit thepassage of fluid therethrough. The end plates 617A are linked to eachother by racks 617B which extend between the end plates 617A. The racks617B are spaced apart from each other. The racks 617B may be attached toan internal surface of the housing 616. Each of the racks 617B includesnotches or grooves 617C spaced apart along the length of the rack 617B.The mesh structure 30 of each perfusion device 20 is removably mountedto the racks 617B by being placed in the grooves 617C.

The bioreactor 10,400 provides a controlled environment. In the depictedembodiment, the internal temperature of the bioreactor 10,400 iscontrolled via a heat exchanger to maintain it constant at 37° C. Theinternal pH of the bioreactor 10,400 is controlled by modulatingbicarbonate to maintain it constant at about 7.4. Since the depictedbioreactor 10,400 is used to process blood plasma, erythrocytes (i.e.red blood cells) are not present in the plasma. Therefore, an oxygencontent of the plasma in the bioreactor 10,400 is controlled. Thebioreactor 10,400 may be used with other types of corporeal fluids, andmay control for fewer or other parameters.

The mesh structure 30 and the encapsulated organ tissues 40 are nowdescribed in greater detail.

Referring to FIGS. 2A and 2B, the mesh structure 30 has a first wall 32spaced apart from a second wall 34 to define an internal mesh cavity 36.The encapsulated organ tissue 40 (not shown in FIGS. 2A and 2B) isdisposed in the internal mesh cavity 36 between the first and secondwalls 32,34. The first and second walls 32,34 are porous to allow thefluid to enter the internal mesh cavity 36 to interact with theencapsulated organ tissue 40. The porous nature of the mesh structure 30is provided by openings 38 in each of the first and second walls 32,34,which permit fluid communication through the mesh structure 30. In FIGS.2A and 2B, the mesh structure 30 includes a base 30A and a cap 30B thatis mountable on the base 30A to close the mesh structure 30 and definethe internal mesh cavity 36. The base 30A includes the first wall 32 ofthe mesh structure 30, and the cap 30B includes the second wall 34. Thecap 30B is press fit onto the base 30A.

Other embodiments of the mesh structure 30 are possible. For example,FIG. 3 shows a one-piece mesh structure 130. The mesh structure 130 iscylindrical, and is shaped as a disc. The first and second walls 132,134are shown spaced apart to define the internal mesh cavity 136. The firstand second walls 132,134 also have openings 138 therein. In FIG. 3 , themesh structure 130 has a side wall 131 with an aperture 133 therein. Theaperture 133 is in fluid communication with the internal mesh cavity136. The aperture 133 allows for the introduction of components makingup the encapsulated organ tissue 40 into the internal mesh cavity 136,as explained in greater detail below. Irrespective of its configuration,the mesh structure 30,130 may have a thickness between about 1 mm andabout 8 mm, and may have a diameter between about 10 mm and about 80 mm.The mesh size (i.e. the size of the openings 38,138) may be betweenabout 500 μm and about 5 mm. Although shown in FIGS. 2A-3 as beingsubstantially circular in shape, it will be appreciated that the meshstructure 30,130 may have other shapes, including but not limited to,rectangular, square, triangular, etc.

Referring to FIG. 4 , the encapsulated organ tissue 40 (sometimesreferred to herein simply as the “EOT 40”) has one or more organoids 42that are at least partially covered with a biocompatible cross-linkedpolymer 44. Each organoid 42 is a grown or cultured mass of cells ortissue that resembles an organ. In FIG. 4 , each organoid 42 is a liverorganoid which resembles the liver, such that the EOT 40 is anencapsulated liver tissue (ELT). The fluid that enters the bioreactor10,400 exchanges compounds with the tissue or cells of the organoids 42within the EOT 40 so that toxic compounds are metabolized by the cellsof the organoids 42 and eliminated in a non-toxic form, while usefulproteins are produced by the cells of the organoids 42 and released intothe fluid. Albumin, ammonia and other plasma constituents that need tobe processed by the liver may therefore be metabolized by the liverorganoids 42, which is similar to human liver function. The organoids 42may also be cultured from the cells or tissues of another organ. Anon-limitative list of other organs whose function can be mimicked bythe organoids 42 includes the kidney, endocrine tissue, and any othertissue that can be perfused by blood and which can be agglomerated intoorganoids 42. It will therefore be appreciated that reference to theliver, liver organoids, or encapsulated liver tissue in the presentdisclosure does not limit the organoids 42 or the EOT 40 to only beingformed from liver cells or tissue.

FIG. 4 shows a process to provide a plurality of monodispersed liverorganoids 42 within the biocompatible and crossed-linked polymer 44. Asshown, hepatoblasts, endothelial progenitor cells and mesenchymalprogenitor cells are obtained from differentiating a single iPSC. Thecells are mixed and co-cultured in suspension to form the liver organoid42. In the embodiment of the liver organoid 42 shown in FIG. 4 , thehepatoblasts have differentiated into hepatocytes which substantiallycover a cellular core formed by mesenchymal and endothelial progenitorcells (prior to the introduction of the liver organoids 42 in theencapsulated liver tissue 40). The embodiment of the liver organoid 42shown in FIG. 4 is substantially spherical in shape and has a relativediameter of about 150 μm. The liver organoids 42 are then encapsulated,using a cross-linking agent, which in FIG. 4 is shown as UV light, in afirst compatible and cross-linkable matrix. The encapsulated livertissue 40 can be used as transplantable liver tissue (having forexample, a size between 5 mm and 10 cm) in regenerative medicine.Alternatively, the liver organoids 42 can be designed to a multiwellplate and used in drug development to determine metabolism orhepatotoxicity of screened compounds.

The polymer 44 (also referred to as a polymeric matrix) that can be usedin the encapsulated liver tissue 40 forms a hydrogel around the liverorganoids 42. A hydrogel refers to polymeric chains that are hydrophilicin which water is the dispersion medium. Hydrogels can be obtained fromnatural or synthetic polymeric networks. In the context of the presentdisclosure, encapsulation within the hydrogel prevents embedded liverorganoids 42 from leaking out of the polymer 44. In an embodiment, eachliver organoid 42 is encapsulated individually and the encapsulatedliver organoids 42 can, in another embodiment, be further included in apolymeric matrix 44. In still another embodiment, the liver organoids 44are included in a polymeric matrix 44 so as to encapsulate them. Asshown in FIG. 4 , the liver organoids 42 encapsulated within thehydrogel material form a disc or other cylindrical structure. Othershapes for the organoids 42 encapsulated within the hydrogel materialare possible and within the scope of the present disclosure. Thehydrogel may be any biocompatible material. Some non-limitative examplesof hydrogels include PEG, and any polyethylene glycol (PEG) basedmaterial such as PEG-vinyl sulfone (PEG-VS).

FIG. 4 shows a process for making the encapsulated organ tissue 40,which is described in PCT patent application PCT/CA2017/051404(published as WO 2018/094522) entitled “Encapsulated Liver Tissue” andfiled Nov. 23, 2017, the entirety of which is incorporated by referenceherein. The organoids 42 may be harvested from the ultra-low attachmentflasks and centrifuged at low speed (400 g for 5 minutes) to form apellet. The pellet (about 3 000 organoids) may be resuspended in 5%4-arm PEG-vinyl sulfone (20 kDa) solution in sterile PBS without calciumand magnesium supplemented with 0.1% N-vinyl-2-pyrrilidone and 0.4 mg/mLIrgacure 2959. A 50 μL droplet of such a solution (containing about 100organoids 42) may be generated and deposed in a well of a 96-well plate,and subsequently cross-linked under UV light (5 minutes 1090 μW/cm² at adistance of 4 cm). The generated encapsulated liver tissue 40 may bemaintained in complete William's E medium/complete EMB2 (1:1) mediumsupplemented with, 20 ng/mL OSM and 10 μM dexamethasone for 5 days. Fivedays after encapsulation, the OSM supplementation may be suspended andthe ratio complete William's E medium/complete EBM2 medium may bechanged from 1:1 to 4:1. The tissue may be cultured at 37° C. in ambientO₂/5% CO₂ and the medium may be changed every other day. Albuminsecretion may be assessed weekly in the conditioned medium. It may bepossible for encapsulated organoids 42 to preserve their ability tosecrete albumin through the hydrogel over more than 7 weeks of culture,proving their survival and maintenance of their differentiated statuswithin the polymer 44 while confirming the diffusion of the secretedprotein outside of it. The encapsulated liver tissue 40 may be solidenough to be manipulated with instruments without losing its shape andintegrity.

FIGS. 5A to 5C show one of the perfusion devices 20 and the EOT 40. TheEOT 40 has a body 46 which provides physical structure to the EOT 40.The body 46 defines a thickness T. The thickness T is defined between afirst surface 48A of the body 46 adjacent to the first wall 32 of themesh structure 30, and a second surface 48B of the body 46 adjacent tothe second wall 34. The EOT 40 is therefore “sandwiched” by the meshstructure 30. In the depicted embodiment, the body 46 takes the form ofthe mesh structure 30, and is thus shaped as a cylinder or disc. Justlike the mesh structure 30, the body 46 may have other shapes, which arepart of the present disclosure. In an embodiment, the thickness T of thebody 46 is between about 1 mm to about 3 mm. Other values for thethickness T of the body 46 are possible and within the scope of thepresent disclosure.

Referring to FIGS. 5B and 5C, the EOT 40 is a three-dimensional porousbody. The EOT 40 is embedded with spatially-organized passages which areperfused with the fluid (e.g. plasma) supplied to the housing 16. Asshown in FIGS. 5B and 5C, the body 46 has one or more channels 41 whichextend into the body 46. Each channel 41 extends into the body 46 fromone or both or the of the first and second surfaces 48A,48B in order toreceive the fluid into the channel 41. Each channel 41 has a diameter D.The diameter D of each channel 41 is selected so that undesirablesolutes within the fluid can be diffused out of the fluid and into thesurrounding tissue of the body 46 to be metabolized. Control over thediameter D of the channels 41 may allow for improved removal ofmolecules of a certain size from the fluid, while allowing molecules ofinterest which have different sizes to remain in the fluid. The diameterD of each channel 41 in the body 46 may be the same, or may vary. In anembodiment, the diameter D of one or more of the channels 41 is betweenabout 150 μm and about 750 μm. Other values for the diameter D of thechannels 41 are possible and within the scope of the present disclosure.

It can therefore be appreciated that each EOT 40 has a vascular-likestructure (i.e. the channels 41) which may assist with penetration ofthe fluid and its solutes within the EOT 40, and with the diffusion ofsolutes out of the fluid into the surrounding polymer 44 hydrogel of thebody 46. This contrasts with some conventional polymerized organ tissueswhich do not have passages, such that the diffusion of solutes islimited to only the surface of the polymerized organ tissue.

The channels 41 may be formed using any suitable technique. Somepossible techniques include photolithography, sacrificial molding, orany other suitable microfabrication technique. When usingphotolithography, for example, forming the channels 41 includes curingportions of the biocompatible cross-linked polymer 44 with a UV lightsource while the body 46 remains in the internal mesh cavity 36 of themesh structure 30. This may include covering the body 46 with aphotomask which has one or more opaque portions which correspond to theultimate location of the channels 41. The biocompatible cross-linkedpolymer 44 is then cured with a UV light source applied to thephotomask. The portions of the body 46 covered by the opaque portions ofthe photomask will remain uncured to thereby form the channels 41 in thebody 46. The EOT 40 may therefore be photopolymerized within the meshstructure 30. If the channels 41 are generated while the polymer 44 isin the mesh structure 30, then the photomask used in photolithographymay need to coordinate the opaque portions with the openings 38 of themesh structure 30 to allow UV light to penetrate to the hydrogel forcuring to occur.

In another embodiment of photolithography within the mesh structure 30,forming the channels 41 includes injecting the at least one liverorganoid 42 and the biocompatible cross-linked polymer 44 into theinternal mesh cavity 36 of the mesh structure, and then curing portionsof the biocompatible cross-linked polymer 44 with a UV light source tosolidify the mass. The portions of the polymer 44 which are not curedform the channels 41. One technique for achieving this result involvespipetting the hydrogel polymer 44 and the organoids 42 into the internalmesh cavity 36 via the openings 38 in the first and second walls 32,34,or via the aperture 133 (see FIGS. 2A to 3 ). Prior to injecting thehydrogel polymer 44 and the organoids 42, both of the first and secondwalls 32,34 and their openings 38 can be sealed, such as with alight-transparent seal like a glass slide. The mixture is then cured andphotopolymerized within the mesh structure 30.

Other techniques for forming the channels 41 are also possible andwithin the scope of the present disclosure. In an alternate embodiment,the EOT 40 is added to the internal mesh cavity 36 of the mesh structure30 after photopolymerization. In yet another embodiment, the body 46 isbio-printed, or formed using a fabricated mold containing the channels41, or by using sacrificial molding of polymers or sugars. In yetanother embodiment, the endothelial progenitor cells of the liverorganoid 42 organise in a capillary or a capillary-like configuration.

The shape, orientation, and path of the channels 41 may vary, and atleast some of these are now described in greater detail.

Referring to FIGS. 5B and 5C, the body 46 includes multiple channels 41.The channels 41A extend through the body 46 between the first and secondsurfaces 48A,48B. The channels 41A therefore communicate the fluidthrough the body 46. A length La of the channels 41A is substantiallyequal to the thickness T of the body 46. The channels 41B also extendthrough the body 46, and also communicate the fluid through the body 46.The length Lb of the channels 41B is greater than the thickness T of thebody 46 because the channels 41B are slanted or inclined with respect tothe first and second surfaces 48A,48B.

Referring to FIGS. 5C and 5D, the through channels 41A,14B allow thefluid to be communicated through the body 46 of one perfusion device 20,and to the body 46A of another, immediately adjacent perfusion device20. The channels 41A,41B of the body 46 are offset from the channels41C,41D of the adjacent body 46A. In the embodiment where the stack ofperfusion devices 20A has an upright orientation, the offset channels41A,41B,41C,41D of the bodies 46,46A are not vertically aligned. Thechannels 41A,41B,41C,41D of the bodies 46,46A do not overlap. The fluidis therefore prevented from flowing directly, in a straight ornon-deviated path, between the bodies 46,46A. The offset channels41A,41B,41C,41D therefore define a winding flow path P for the fluid,such that the fluid is deviated from a straight-line path between thebodies 46,46A. In FIG. 5D, one of the winding flow paths P allows thefluid to enter the channel 41A and flow through the body 46, and thenflow along the first surface 48A of the body 46A until arriving at thechannel 41C, at which point the fluid enters the channel 41C and flowsthrough the body 46A. This deviation of the fluid from one perfusiondevice 20 to the next may help to increase the chance of solutesdiffusing out of the fluid by delaying diffusion and giving the fluidmore time to interact with the organoids 42 of the EOT 40.

FIG. 6 shows another configuration of the channels 141 of the EOT 40.The channels 141 include a first or primary channel 141A and one or moreother channels 141, referred to as secondary channels 141B. The primarychannel 141A is a through-channel, and extends through the body 46between the first and second surfaces 48A,48B. The secondary channels141B extend into the body 46 from a first end 149A at one of the firstand second surfaces 48A,48B, to a second end 149B within the body 46 atthe primary channel 141A. The second end 149B of the secondary channels141B opens into the primary channel 141A, such that the secondarychannel 141B is in fluid communication with the primary channel 141A.The fluid may therefore be conveyed from the first or second surface48A,48B of the body 46, through the secondary channels 141B, and intothe primary channel 141A. The length La of the primary channel 141A issubstantially equal to, or greater than, the thickness T of the body 46.The length Lb of the secondary channels 141B is either less than thethickness T of the body 46, or greater than the thickness T of the body46. The length Lb′ of the secondary channel 141B is less than thethickness T of the body 46. The length Lb″ of the secondary channel 141Bis greater than the thickness T of the body 46, such that this secondarychannel 141B follows a meandering, winding, or serpentine path throughthe body 46. The secondary channel 141B′″ is a “dead-end” channel, andextends into the body 46 from one of the first and second surfaces48A,48B to a second end 149B within the body 46 that is not in fluidcommunication with any other channels 141A,141B. The dead-end secondarychannel 141B′″ may diffuse solvents out of the fluid and into the body46.

FIG. 7 shows another configuration of the channels 241 of the EOT 40.The body 46 includes two primary channels 241A. Each primary channel241A extends into the body 46 from one of the first and second surfaces48A,48B. Each primary channel 241A is a “dead-end” channel, and does notextend through the body 46. One or more secondary channels 241B extendbetween the two primary channels 241A to fluidly connect them. The fluidis therefore able to pass through the body 46 from each of the first andsecond surfaces 48A,48B by flowing into one of the primary channels241A, through one or more secondary channels 241B, and out the otherprimary channel 241A.

Referring to FIGS. 1A and 1B, the operation of the bioreactor 10 isexplained in greater detail. The fluid received at the housing inlet 18Aof the housing 16 is conveyed into the internal cavity 19 to perfuse thefluid to the EOT 40 of each perfusion device 20. The fluid is thereforedelivered through the openings 38 in the first and second walls 32,34 ofeach mesh structure 30 to the organoids 42 and the channels 41 of eachEOT 40. In the depicted embodiment, the fluid is conveyed againstgravity, from the lower housing inlet 18A to the higher housing outlet18B. As shown in FIG. 1B, the housing 16 has multiple supports 17 whichare attached to the inner surface 19A and spaced apart along the lengthL of the housing 16. The mesh structure 30 of each perfusion device 20is removably mounted to one of the supports 17. In the depictedembodiment, the supports 17 are notches or grooves in parallel columns17A which are attached to the inner surface 19A, and which extend alongthe length L of the housing 16. The columns 17A are supported withsieves to prevent organoids 42 from the EOT 40 from escaping into theprocessed fluid leaving the fluid outlet 18B in case of tissue breakage.Other configurations for the supports 17 are possible and within thescope of the present disclosure. For example, in any alternateembodiment, each mesh structure 30 has one or more supports 17 forattaching to the inner surface 19A of the housing 16.

Still referring to FIG. 1B, the stack of perfusion devices 20A may becryopreserved. All materials used may withstand extremely lowtemperatures without or with minimal fatigue. Prior to starting plasmatherapy, the perfusion devices 20 may be taken out of cryopreservationand inserted into the bioreactor 10. Circulation of warm fluid (e.g.warm plasma) can thaw the organoids 42 in the bioreactor 10 and furthermaintain the temperature of the organoids 42 at body temperature,creating an optimal environment for the tissue. In an embodiment,between about 0.1% and about 1% of the mass of a human liver is presentin the perfusion devices 20 of the housing 16. This equates toapproximately from a few million to a few billion liver cells, and mayalso equate to between about 500 to about 10,000 organoids per perfusiondevice 20.

FIG. 8 shows an embodiment of an artificial liver system 300 having thebioreactor 10,400 described herein. The artificial liver system 300helps to mimic the function of the human liver, and may therefore bereferred to as a “Bio-Artificial Liver Device (BALD)”. The artificialliver system 300 (sometimes referred to herein simply as the “system300”) includes a fluid network 302, which is a series of tubes,connectors, and other components to communicate blood plasma between thefeatures of the system 300. The system 300 has a peristaltic pump 304 tocirculate the plasma through the fluid network 302. In the depictedembodiment, the pump 304 pushes plasma through the fluid network 302 ata flow rate of between about 50 mL/min to about 300 mL/min. Infusionpumps may be placed right after the pump 304 to insert saline and/or ananticoagulant (Heparin). The fluid network 302 may have a pressuresensor to determine pressure across the system 300, and to ensure thatplasma re-enters the patient at a pressure similar to that at which itwas extracted.

The system 300 may optionally have an adsorbent cartridge, shown in FIG.8 as a molecular adsorbent system 306, or MAS. The MAS 306 is anysuitable perfusion device or charcoal adsorbent system. The MAS 306 isin fluid communication with the fluid network 302 to remove some of theundesired solutes from the plasma. The undesired solutes may includetoxins, and high levels of bilirubin. The undesired solutes are removedfrom the plasma in the MAS 306 using adsorption on an activated charcoalor hydrophobic resin. The system 300 may also have an oxygenator 308 influid communication with the fluid network 302, as shown in FIG. 8 . Theoxygenator 308 operates to dissolve oxygen into the plasma to produceoxygenated plasma. The bioreactor 10,400 is shown in fluid communicationwith the oxygenator 308, and receives the oxygenated plasma therefrom.The oxygenated plasma enters the bioreactor 10,400 and interacts withthe ELTs 40 of the perfusion devices 20, which operate to diffuse otherremaining undesired solutes, not already removed by the MAS 306, out ofthe oxygenated plasma and into the body 46 of the EOT 40. In analternate embodiment, the oxygenator 308 is a component of thebioreactor 10,400, and oxygenation is performed in the bioreactor 10,400itself. In an embodiment, the system 300 is free of an oxygenator. In anembodiment, oxygenation is performed on the plasma downstream of thebioreactor 10,400. The processed plasma exiting the housing outlet 18Bof the bioreactor 10,400 may be provided to attach to acommercially-available extracorporeal filtration system 310. The system300 in FIG. 8 may therefore be an add-on device to be used with theexisting extracorporeal filtration system 310. In an alternateembodiment, a dialyzer 416 (see FIG. 9 ) is placed in the system 300after the bioreactor 10,400 to perform plasma dialysis.

FIG. 9 shows another embodiment of an artificial liver system 400 havingthe bioreactor 10,400 described herein. The system 400 is a stand-aloneextracorporeal unit which includes a blood circuit 401A and a plasmacircuit 401B. The blood circuit 401A includes a pump 402 to pump bloodinto the system 400. Infusion pumps 402A are placed right after the pump402 to insert saline and an anticoagulant (Heparin). In FIG. 9 , the MAS406 is positioned in the blood circuit 401A before a plasmafractionation module 408 which separates the plasma from the blood, andwhich provides the plasma to the plasma circuit 401B. In the plasmacircuit 401B, the system 400 has a peristaltic pump 410 to circulate theplasma through the fluid network 412. A blood leak detector 414 ispresent before the dialyzer 416 of the plasma circuit 401B, whichremoves some of the undesired solutes from the plasma using a dialysate.The plasma circuit 401B also has an oxygenator 418 to dissolve oxygeninto the plasma to produce oxygenated plasma. The bioreactor 10,400 isin fluid communication with the oxygenator 418, and receives theoxygenated plasma therefrom. The oxygenated plasma enters the bioreactor10,400 and interacts with the ELTs 40 of the perfusion devices 20, whichoperate to diffuse other, remaining undesired solutes, not alreadyremoved by the MAS 406 or the dialyzer 416, out of the oxygenated plasmaand into the bodies 46 of the EOTs 40. The processed plasma exiting thehousing outlet 18B of the bioreactor 10,400 is provided back to theblood circuit 401A, where it is recombined with the separated bloodproducts and returned to the patient's blood, or further fluidprocessing may be performed. The blood circuit 401A has an air bubbledetector 420 to prevent air from being introduced into the blood. Thesystem 400 may also include temperature sensor(s), flow meter(s), a cellfilter(s), heat exchanger(s) to maintain a constant temperature,clamp(s), drip chamber(s), and any other suitable devices.

FIG. 10 shows another embodiment of an artificial liver system 500having the bioreactor 10,400 described herein. The system 500 is astand-alone extracorporeal unit which includes a blood circuit 501A anda plasma circuit 501B. The blood circuit 501A includes a pump 502 topump blood into the system 500. Infusion pumps 502A are placed rightafter the pump 502 to insert saline and an anticoagulant (Heparin). Aplasma fractionation module 508 separates the plasma from the blood, andprovides the plasma to the plasma circuit 501B. In the plasma circuit501B, the system 500 has a peristaltic pump 510 to circulate the plasmathrough the fluid network 512. A blood leak detector 514 is presentupstream of the pump 510. The plasma circuit 501B also has an oxygenator518 to dissolve oxygen into the plasma to produce oxygenated plasma. Thebioreactor 10,400 is in fluid communication with the oxygenator 518, andreceives the oxygenated plasma therefrom. The oxygenated plasma entersthe bioreactor 10,400 and interacts with the ELTs 40 of the perfusiondevices 20, which operate to diffuse remaining undesired solutes out ofthe oxygenated plasma and into the bodies 46 of the EOTs 40. Theprocessed plasma exiting the housing outlet 18B of the bioreactor 10,400is provided back to the blood circuit 501A, and then to the dialyzer516, which removes some of the undesired solutes from the plasma using adialysate. The treated plasma is recombined with the separated bloodproducts and returned to the patient's blood, or further fluidprocessing may be performed. The blood circuit 501A has an air bubbledetector 520 to prevent air from being introduced into the blood. Thesystem 500 may also include temperature sensor(s), flow meter(s), a cellfilter(s), heat exchanger(s) to maintain a constant temperature,clamp(s), drip chamber(s), and any other suitable devices. The system500 may include a hemoperfusion (HP) cartridge, as shown in FIG. 10 ,which may be positioned upstream of the bioreactor 10,400.

Embodiments disclosed herein include:

A. A perfusion bioreactor, comprising: a housing having a length definedbetween a housing inlet and a housing outlet, the housing having aninner surface delimiting an internal cavity of the housing disposedbetween the housing inlet and the housing outlet and in fluidcommunication therewith; and perfusion devices disposed in the internalcavity of the housing, each of the perfusion devices comprising: a meshstructure supported from the inner surface of the housing, the meshstructure having a first wall spaced apart from a second wall to definean internal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated organ tissue disposed in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated organ tissue having at least one organoid atleast partially covered with a biocompatible cross-linked polymer, theencapsulated organ tissue having a body with a thickness defined betweena first surface of the body adjacent the first wall of the meshstructure and a second surface of the body adjacent the second wall ofthe mesh structure, the body having at least one channel extending intothe body from one of the first and second surfaces to receive a fluidtherein, the at least one channel having a diameter selected to diffusesolutes out of the fluid and into the body; the perfusion devices beingdisposed in the internal cavity of the housing one adjacent to anotherand spaced apart from each other along the length of the housing toreceive the fluid conveyed from the housing inlet to the housing outlet,and to perfuse the fluid to the encapsulated organ tissue of eachperfusion device and to the at least one channel therein.

B. A perfusion device, comprising: a mesh structure having a first wallspaced apart from a second wall to define an internal mesh cavity, eachof the first and second walls of the mesh structure having openingstherein to permit fluid communication through the mesh structure; and anencapsulated organ tissue disposed in the internal mesh cavity betweenthe first and second walls of the mesh structure, the encapsulated organtissue having at least one organoid at least partially covered with abiocompatible cross-linked polymer, the encapsulated organ tissue havinga body with a thickness defined between a first surface of the bodyadjacent the first wall of the mesh structure and a second surface ofthe body adjacent the second wall of the mesh structure, the body havingat least one channel extending into the body from one of the first andsecond surfaces to receive a fluid therein, the at least one channelhaving a diameter selected to diffuse solutes out of the fluid and intothe body.

C. An artificial liver system, comprising: a fluid network and a pump tocirculate plasma through the fluid network; and a perfusion bioreactorin fluid communication with the fluid network to receive the plasmatherefrom, the perfusion bioreactor comprising: a housing having alength defined between a housing inlet and a housing outlet, the housinghaving an inner surface delimiting an internal cavity of the housingbetween the housing inlet and the housing outlet and in fluidcommunication therewith, the housing inlet receiving the plasma; and aplurality of perfusion devices disposed in the internal cavity of thehousing, each of the perfusion devices comprising: a mesh structuresupported from the inner surface of the housing, the mesh structurehaving a first wall spaced apart from a second wall to define aninternal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated liver tissue disposed in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated liver tissue having at least one liverorganoid at least partially covered with a biocompatible cross-linkedpolymer, the encapsulated liver tissue having a body with a thicknessdefined between a first surface of the body adjacent the first wall ofthe mesh structure and a second surface of the body adjacent the secondwall of the mesh structure, the body having at least one channelextending into the body from one of the first and second surfaces toreceive the plasma therein, the at least one channel having a diameterselected to diffuse undesired solutes out of the plasma and into thebody; the perfusion devices being disposed in the internal cavity of thehousing one adjacent to another and spaced apart from each other alongthe length of the housing to receive the plasma conveyed from thehousing inlet to the housing outlet, and to perfuse the plasma to theencapsulated liver tissue of each perfusion device and to the at leastone channel therein.

D. A method of processing blood plasma, comprising: conveying the bloodplasma to at least one channel formed in an encapsulated liver tissuehaving at least one liver organoid at least partially covered with abiocompatible cross-linked polymer, the at least one channel having adiameter selected to diffuse undesired solutes out of the blood plasmaand into the encapsulated liver tissue.

E. A method of making a perfusion device, comprising: providing at leastone liver organoid at least partially covered with a biocompatiblecross-linked polymer, the at least one liver organoid at least partiallycovered with the biocompatible cross-linked polymer having a body withat least one channel extending into the body, the at least one channelhaving a diameter selected to diffuse solutes out of a fluid and intothe body; and positioning the body within a cavity of a mesh structureto allow the fluid to enter the cavity and the at least one channel ofthe body, and to exit the cavity.

Each of the embodiments A, B, C, D and E may have one or more of thefollowing additional elements in any combination.

Element 1: the at least one channel of the body of each perfusion deviceextends through the body between the first and second surfaces.

Element 2: a length of the at least one channel is substantially equalto, or greater than, the thickness of the body.

Element 3: the at least one channel of one of the perfusion devices isoffset from the at least one channel of an immediately adjacentperfusion device, the fluid following a winding flow path between thechannels of the adjacent perfusion devices.

Element 4: the at least one channel of the body includes a first channeland at least another channel, the first channel extending through thebody between the first and second surfaces, the at least another channelextending into the body from a first end at one of the first and secondsurfaces to a second end within the body at the first channel, the atleast another channel being in fluid communication with the firstchannel.

Element 5: a length of the first channel is substantially equal to, orgreater than, the thickness of the body, and a length of the at leastanother channel is less than or greater than the thickness of the body.

Element 6: the length of the at least another channel is greater thanthe thickness of the body.

Element 7: a plurality of supports spaced apart along the length of thehousing, the mesh structure of each perfusion device being removablymounted to one of the supports.

Element 8: the housing has an upright orientation, the perfusion devicesbeing supported from the housing one on top of another in a stack.

Element 9: the diameter of the at least one channel is between 150 μmand 750 μm.

Element 10: the at least one organoid of the encapsulated organ tissueincludes a plurality of liver organoids.

Element 11: conveying the oxygenated blood plasma includes conveying theoxygenated blood plasma from the at least one channel to a secondchannel in another encapsulated liver tissue having at least one liverorganoid at least partially covered with the biocompatible cross-linkedpolymer.

Element 12: conveying the oxygenated blood plasma includes conveying theoxygenated blood plasma from the at least one channel to a secondchannel in another encapsulated liver tissue having at least one liverorganoid at least partially covered with the biocompatible cross-linkedpolymer, the second channel being misaligned with the at least onechannel.

Element 13: conveying the oxygenated blood plasma from the at least onechannel to the second channel includes conveying the oxygenated bloodplasma to the second channel being vertically spaced apart from the atleast one channel.

Element 14: cryopreserving the encapsulated liver tissue prior toconveying the blood plasma through the fluid network.

Element 15: warming the cryopreserved encapsulated liver tissue with theoxygenated blood plasma

Element 16: providing the at least one liver organoid at least partiallycovered with the biocompatible cross-linked polymer includes forming theat least one channel in the body using photolithography.

Element 17: forming the at least one channel includes curing portions ofthe biocompatible cross-linked polymer with a UV light source while thebody remains in the cavity of the mesh structure.

Element 18: forming the at least one channel includes injecting the atleast one liver organoid and the biocompatible cross-linked polymer intothe cavity of the mesh structure, and curing portions of thebiocompatible cross-linked polymer with a UV light source.

Element 19: forming the at least one channel includes covering the bodywith a photomask having at least one opaque portion, and curing thebiocompatible cross-linked polymer with a UV light source applied to thephotomask, a portion of the body covered by the at least one opaqueportion of the photomask remaining uncured to form the at least onechannel.

Element 20: oxygenating the blood plasma to produce oxygenated bloodplasma.

Element 21: oxygenating the blood plasma includes oxygenating the bloodplasma before conveying the blood plasma to the at least one channel.

Element 22: oxygenating the blood plasma includes oxygenating the bloodplasma in a perfusion bioreactor.

Element 23: an oxygenator in fluid communication with the fluid networkto diffuse oxygen into the plasma to produce oxygenated plasma.

The above description is meant to be exemplary only, and one skilled inthe art will recognize that changes may be made to the embodimentsdescribed without departing from the scope of the invention disclosed.Still other modifications which fall within the scope of the presentinvention will be apparent to those skilled in the art, in light of areview of this disclosure, and such modifications are intended to fallwithin the appended claims.

The invention claimed is:
 1. A perfusion bioreactor, comprising: ahousing having a length defined between a housing inlet and a housingoutlet, the housing having an inner surface delimiting an internalcavity of the housing disposed between the housing inlet and the housingoutlet and in fluid communication therewith; and perfusion devicesdisposed in the internal cavity of the housing, each of the perfusiondevices comprising: a mesh structure supported from the inner surface ofthe housing, the mesh structure having a first wall spaced apart from asecond wall to define an internal mesh cavity, each of the first andsecond walls of the mesh structure having openings therein to permitfluid communication through the mesh structure; and an encapsulatedorgan tissue disposed in the internal mesh cavity between the first andsecond walls of the mesh structure, the encapsulated organ tissue havingat least one organoid at least partially covered with a biocompatiblecross-linked polymer, the encapsulated organ tissue having a body with athickness defined between a first surface of the body adjacent the firstwall of the mesh structure and a second surface of the body adjacent thesecond wall of the mesh structure, the body having at least one channelextending into the body from one of the first and second surfaces toreceive a fluid therein, the at least one channel having a diameterselected to diffuse solutes out of the fluid and into the body; theperfusion devices being disposed in the internal cavity of the housingone adjacent to another and spaced apart from each other along thelength of the housing to receive the fluid conveyed from the housinginlet to the housing outlet, and to perfuse the fluid to theencapsulated organ tissue of each perfusion device and to the at leastone channel therein.
 2. The perfusion bioreactor of claim 1, wherein theat least one channel of the body of each perfusion device extendsthrough the body between the first and second surfaces.
 3. The perfusionbioreactor of claim 2, wherein a length of the at least one channel issubstantially equal to, or greater than, the thickness of the body. 4.The perfusion bioreactor of claim 2, wherein the at least one channel ofone of the perfusion devices is offset from the at least one channel ofan immediately adjacent perfusion device, the fluid following a windingflow path between the channels of the adjacent perfusion devices.
 5. Theperfusion bioreactor of claim 1, wherein the at least one channel of thebody includes a first channel and at least another channel, the firstchannel extending through the body between the first and secondsurfaces, the at least another channel extending into the body from afirst end at one of the first and second surfaces to a second end withinthe body at the first channel, the at least another channel being influid communication with the first channel.
 6. The perfusion bioreactorof claim 5, wherein a length of the first channel is substantially equalto, or greater than, the thickness of the body, and a length of the atleast another channel is less than or greater than the thickness of thebody.
 7. The perfusion bioreactor of claim 6, wherein the length of theat least another channel is greater than the thickness of the body. 8.The perfusion bioreactor of claim 1, comprising a plurality of supportsspaced apart along the length of the housing, the mesh structure of eachperfusion device being removably mounted to one of the supports.
 9. Theperfusion bioreactor of claim 1, wherein the housing has an uprightorientation, the perfusion devices being supported from the housing oneon top of another in a stack.
 10. The perfusion bioreactor of claim 1,wherein the diameter of the at least one channel is between 150 μm and750 μm.
 11. The perfusion bioreactor of claim 1, wherein the at leastone organoid of the encapsulated organ tissue includes a plurality ofliver organoids.
 12. A method of making a perfusion device, comprising:providing at least one liver organoid at least partially covered with abiocompatible cross-linked polymer, the at least one liver organoid atleast partially covered with the biocompatible cross-linked polymerhaving a body with at least one channel extending into the body, the atleast one channel having a diameter selected to diffuse solutes out of afluid and into the body; and positioning the body within a cavity of amesh structure to allow the fluid to enter the cavity and the at leastone channel of the body, and to exit the cavity.
 13. The method of claim12, wherein providing the at least one liver organoid at least partiallycovered with the biocompatible cross-linked polymer includes forming theat least one channel in the body using photolithography.
 14. The methodof claim 13, wherein forming the at least one channel includes curingportions of the biocompatible cross-linked polymer with a UV lightsource while the body remains in the cavity of the mesh structure. 15.The method of claim 12, wherein forming the at least one channelincludes injecting the at least one liver organoid and the biocompatiblecross-linked polymer into the cavity of the mesh structure, and curingportions of the biocompatible cross-linked polymer with a UV lightsource.
 16. The method of 13, wherein forming the at least one channelincludes covering the body with a photomask having at least one opaqueportion, and curing the biocompatible cross-linked polymer with a UVlight source applied to the photomask, a portion of the body covered bythe at least one opaque portion of the photomask remaining uncured toform the at least one channel.
 17. The method of claim 12, comprisingcryopreserving the at least one liver organoid at least partiallycovered with the biocompatible cross-linked polymer.
 18. The method ofclaim 17, comprising warming the cryopreserved at least one liverorganoid at least partially covered with the biocompatible cross-linkedpolymer with a blood plasma.
 19. A perfusion device, comprising: a meshstructure having a first wall spaced apart from a second wall to definean internal mesh cavity, each of the first and second walls of the meshstructure having openings therein to permit fluid communication throughthe mesh structure; and an encapsulated organ tissue positionable in theinternal mesh cavity between the first and second walls of the meshstructure, the encapsulated organ tissue having at least one organoid atleast partially covered with a biocompatible cross-linked polymer, theencapsulated organ tissue being a three-dimensional porous bodypositionable adjacent the first and second walls of the mesh structure,the three-dimensional porous body defining a vascular-like structureconfigured to receive a fluid therein, the vascular-like structureselected to diffuse solutes out of the fluid and into surroundingpolymer of the three-dimensional porous body.
 20. The perfusion deviceof claim 19, wherein the vascular-like structure includes at least onechannel extending into or through the three-dimensional porous body, theat least one channel configured to receive the fluid therein, the atleast one channel having a diameter selected to diffuse solutes out ofthe fluid and into the surrounding polymer of the three-dimensionalporous body.